CN112773484A - 椎骨重建植入物 - Google Patents

椎骨重建植入物 Download PDF

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Publication number
CN112773484A
CN112773484A CN202010000574.4A CN202010000574A CN112773484A CN 112773484 A CN112773484 A CN 112773484A CN 202010000574 A CN202010000574 A CN 202010000574A CN 112773484 A CN112773484 A CN 112773484A
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China
Prior art keywords
flexible body
vertebral
reconstruction implant
vertebral reconstruction
implant
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CN202010000574.4A
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CN112773484B (zh
Inventor
张方杰
蔡佩宜
林得耀
陈安利
曾峰毅
黄志杰
沈欣欣
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Industrial Technology Research Institute ITRI
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Industrial Technology Research Institute ITRI
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Abstract

本发明公开一种椎骨重建植入物，包含一可挠性主体以及至少一螺钉接头。可挠性主体为一体成型的单体结构具有彼此相连通的至少一接头组装槽以及至少一开口。螺钉接头为一体成型的单体结构且可活动地容置于接头组装槽中。

Description

椎骨重建植入物
技术领域
本发明涉及一种植入物，特别是涉及一种椎骨重建植入物。
背景技术
脊椎骨缺陷、损伤可能由先天性缺陷、肿瘤或其他疾病、衰老或创伤所引起。通常的治疗手段是对受损或具有肿瘤的椎骨(vertebra)切除并进行重建手术。手术过程中，医师会使用椎根螺钉(pedicle screw)和脊椎固定杆(spine fixation rod)将脊柱对齐并将受损的椎骨切除，再将植入物置入移除椎骨后的空间以对其进行重建。
但目前市售用于重建椎骨的植入物存在许多问题。举例来说，现有的椎骨重建植入物通常具有较高的刚性及不足的可挠性，但椎骨的质地相对较软，因此术后常常出现植入物压迫甚至使邻接椎骨凹陷、损伤等问题，陷入椎骨的植入物不仅无法再维持椎骨于所需的高度，受损的椎骨还会产生病变或退化等后遗症。
这个情况在人体进行活动时更为严重，人体于日常活动时会增加椎骨之间的压力，刚性过高且缺乏可挠性的植入物会容易与椎骨之间产生应力集中的现象，从而促使植入物破坏椎骨的情况。并且，由于可挠性不足，因此现有的植入物常常无法配合人体活动时椎骨所需要的移动而容易发生植入物从椎骨间滑脱的问题，从而导致融合失败的结果。
此外，基于一些原因，目前有些植入物的外形设计为简单的圆筒状，置入椎骨间后容易使应力集中在椎骨中心处质地更为脆弱的部位，从而更加剧前述植入物破坏椎骨并陷入椎骨等问题。
发明内容
有鉴于此，本发明提供一种椎骨重建植入物，具有足够的可挠性以降低其与邻接椎骨的应力集中问题以及配合人体日常活动时邻接椎骨所需的移动。
根据本发明的一实施例所揭露的一种椎骨重建植入物，包含一可挠性主体以及至少一螺钉接头。可挠性主体为一体成型的单体结构具有彼此相连通的至少一接头组装槽以及至少一开口。螺钉接头为一体成型的单体结构且可活动地容置于接头组装槽中。
根据本发明前述实施例所揭露的椎骨重建植入物，通过一体成型的可挠性主体，使得椎骨重建植入物具有足以维持椎骨相对位置的刚性的同时，还具有可配合人体活动的可挠性与可压缩性，以减低或缓冲人体活动时来自椎骨的压力，不仅可避免从椎骨间滑脱的问题，还可避免与邻接的椎骨之间产生应力集中而破坏椎骨的问题。由此，可避免椎骨重建手术后如椎骨受损病变或退化、植入物滑脱或融合失败等问题的发生。
并且，通过一体成型且可活动地位于可挠性主体中的螺钉接头，便于医师于手术过程中调整椎根螺钉的角度，从而助于手术的进行。
以上的关于本发明揭露内容的说明及以下的实施方式的说明，用以示范与解释本发明的精神与原理，并且提供本发明的权利要求更进一步的解释。
附图说明
图1为本发明的一实施例的椎骨重建植入物的使用情境示意图；
图2为图1的椎骨重建植入物的侧视图；
图3为图2的椎骨重建植入物的立体分解示意图；
图4为图2的椎骨重建植入物的局部放大示意图；
图5为图1的椎骨重建植入物受力时的示意图；
图6为本发明的另一实施例的椎骨重建植入物的侧视图；
图7A为本发明的又一实施例的椎骨重建植入物的立体分解示意图；
图7B为图7A的椎骨重建植入物的使用示意图；
图8A为本发明的再一实施例的椎骨重建植入物的立体示意图；
图8B为图8A的椎骨重建植入物的使用示意图。
符号说明
1a～1d 椎骨重建植入物
10a～10b 可挠性主体
10c～10d 第一可挠性主体
11c～11d 第二可挠性主体
20 螺钉接头
30c～30d 衔接件
91 椎骨
81 椎根螺钉
82 脊椎固定杆
100 椎骨接触面
101 沟槽
102 可变形部
103 接头组装槽
104 开口
105 牙状结构
107 多孔结构
108 螺钉抵接内壁面
210 显露部
211 锁孔
220 嵌入部
310c、310d 衔接杆部
320c、320d 间隔部
具体实施方式
以下在实施方式中详细叙述本发明的详细特征以及优点，其内容足以使任何熟悉相关技术者，了解本发明的技术内容并据以实施，且根据本说明书所揭露的内容、权利要求及附图，任何熟悉相关技术者可轻易地理解本发明相关的目的及优点。以下的实施例进一步详细说明本发明的观点，但非以任何观点限制本发明的范畴。
此外，以下将以附图揭露本发明的实施例，为明确说明起见，许多实务上的细节将在以下叙述中一并说明。然而，应了解到的是，这些实务上的细节非用以限制本发明。
并且，为达图面整洁的目的，一些现有惯用的结构与元件在附图可能会以简单示意的方式绘示之。另外，本案的附图中部分的特征可能会略为放大或改变其比例或尺寸，以达到便于理解与观看本发明的技术特征的目的，但这并非用于限定本发明。依照本发明所揭露的内容所制造的产品的实际尺寸与规格应是可依据生产时的需求、产品本身的特性、及搭配本发明如下所揭露的内容据以调整，于此先声明之。
另外，以下文中可能会使用「端」、「部」、「部分」、「区域」、「处」等术语来描述特定元件与结构或是其上或其之间的特定技术特征，但这些元件与结构并不受这些术语所限制。在下文中，也可能会使用「及/或(and/or)」的术语，其是指包含了一或多个所列相关元件或结构的其中一者或全部的组合。以下文中也可能使用「实质上」、「基本上」、「约」或「大约」等术语，其与尺寸、浓度、温度或其他物理或化学性质或特性的范围结合使用时，为意欲涵盖可能存在于该等性质或特性的范围的上限及/或下限中的偏差、或表示容许制造公差或分析过程中所造成的可接受偏离，但仍可达到所预期的效果。
再者，除非另有定义，本文所使用的所有词汇或术语，包括技术和科学上的词汇与术语等具有其通常的意涵，其意涵能够被熟悉此技术领域者所理解。更进一步的说，上述的词汇或术语的定义，在本说明书中应被解读为与本发明相关技术领域具有一致的意涵。除非有特别明确的定义，这些词汇或术语将不被解释为过于理想化的或正式的意涵。
首先，请参阅图1，本发明的一实施例提出一种椎骨重建植入物(vertebrareconstruction implant)1a，如图所示，椎骨重建植入物1a适于植入于移除某一节椎骨(vertebra)91后所产生的空间，即适于置入椎骨91之间，以取代并重建所移除的椎骨91。此外，椎骨重建植入物1a还可搭配椎根螺钉(pedicle screw)81与脊椎固定杆(spinefixation rod)82一同使用，以维持其与相邻的椎骨91的相对位置关系。
在本实施例与其他实施例中，椎骨重建植入物1a可以但不限于是以3D打印技术所制造，且其材料可以但不限于具有生物相容性及足以支撑椎骨91所需的刚性，如钛合金、铁基合金、钴合金、高分子材料、陶瓷或其复合材料，但本发明并非以此为限。
补充说明的是，为提升椎骨重建植入物1a与人体组织的相融性，椎骨重建植入物1a可于成型时使其具有粗糙表面，但为达附图简洁的目的，图1及以下附图并无对此进行绘示。同时，搭配椎骨重建植入物1a的结构设计，椎骨重建植入物1a除了可有效与邻接的椎骨91相融合，椎骨重建植入物1a还具有足够的刚性以在椎骨91之间提供足够的支撑力，但又同时具有多方向性地可挠性及可压缩性，以配合人体运动时椎骨91间产生的相对位置改变，从而避免传统的植入物容易产生的滑脱或压损椎骨等问题。
详细来说，请参阅图2～图4，图2为图1的椎骨重建植入物1a的侧视图，图3为图2的椎骨重建植入物1a的立体分解示意图，而图4为图2的椎骨重建植入物1a的局部放大示意图。在本实施例与其他实施例中，椎骨重建植入物1a至少可包含一可挠性主体10a以及二螺钉接头20。可挠性主体10a大致上为轮廓不规则的柱体，且为一体成型的单体结构，可挠性主体10a具有彼此相对的二椎骨接触面100，分别用以抵接相邻的椎骨(如前述图1的椎骨91)。
于此，补充说明的是，一般来说，椎骨如同其他骨骼组织，具有外圈质地较硬的皮质骨(cortical bone)以及中心处质地较软且类似海绵的松质骨(cancellous bone)，为了配合这样骨骼组织，在本实施例与其他实施例中，可挠性主体10a于成型时，可依据所欲邻接的椎骨的实际情况将外形进行客制化，以使其椎骨接触面100的范围至少扩及椎骨的皮质骨且具有相似于皮质骨的形状的外轮廓，除了可使椎骨重建植入物1a与椎骨之间的应力分散较为平均，还可使椎骨接触面100至少接触椎骨的皮质骨以避免应力集中在质地较软的松质骨。
此外，可挠性主体10a的结构设计使其整体具有可压缩性及可挠性，如图所示，可挠性主体10a上可具有多个沟槽101，这些沟槽101彼此不相连地交错排列，以使得可挠性主体10a具有多个彼此保持一特定距离(即沟槽101)的可变形部102。于附图垂直方向来看，可变形部102悬置于另一可变形部102上方，因此，当一程度的外力施加于可变形部102时，可使其产生形变而相对周围的可变形部102产生微幅的弯曲。
补充说明的是，在一些实施例中，就沟槽101的配置来说，沟槽101在其所处的平面上可占可挠性主体10a于该平面的周长的约50～99％，每一层可变形部102上方与下方的沟槽101相对于可挠性主体10a的中心线的相位差可为0～180度，但本发明并非以此为限，可挠性主体上的沟槽的长度、配置方式等均可依据实际需求进行设计上的调整。
此外，为了加强可挠性主体10a与椎骨91之间的结合强度以避免滑脱等情况发生，在本实施例或其他实施例中，可挠性主体10a还可具有多个牙状结构105，这些牙状结构105突设于椎骨接触面100，可咬入邻接的椎骨91中。值得注意的是，如图3所示，在本实施例与其他实施例中，牙状结构105是位于椎骨接触面100较***的部位且沿着椎骨接触面100外轮廓进行配置，由前述可知，牙状结构105的排列方式可对应椎骨的皮质骨，因此牙状结构105主要是咬合于椎骨中质地较硬的部分，有助于避免应力集中在质地较软的松质骨以及降低对椎骨可能造成的影响。
然而，牙状结构105于椎骨接触面100上的配置方式也可以改为是阵列式或随机分布等方式，本发明并非以此为限。此外，牙状结构105的高度可约为0.5～3毫米，其斜边相对于椎骨接触面100的斜率可约为20～70度，但这些数值均可依据实际需求再进行调整，本发明亦以此为限。
另外，在本实施例或其他实施例中，可挠性主体10a上可以但不限于具有多孔结构107，可作为周围人体组织往椎骨重建植入物1a内部生长的通道，有助于增加人体组织在椎骨重建植入物1a中可增生的空间，从而有助于提升椎骨重建植入物1a与人体组织的相融性。在此情况下，可挠性主体10a中部分或全部的可变形部102可以但不限于都形成有多孔结构107。在本实施例或其他实施例中，多孔结构107的数量可达到占可挠性主体10a的体积百分比约20～80％的程度。
此外，补充说明的是，本发明并非以多孔结构107的孔洞大小、形状或孔洞之间的距离等为限，这些均可依据实际需求进行调整。例如多孔结构107的形状可以但不限于是格子形或如海绵般不规则形。另外，多孔结构107在可挠性主体10a中的疏密程度也可依据实际需求进行设计上的调整，也就是说，可挠性主体10a中有些区域可相较于其他区域具有数量较多的多孔结构107。然而，为达附图简洁的目的，图3以及其他附图仅于椎骨接触面100上绘示多孔结构107。
在本实施例与其他实施例中，可挠性主体10a还可供螺钉接头20设置。具体来说，如图所示，可挠性主体10a还可具有二接头组装槽103，螺钉接头20分别可活动地容置于可挠性主体10a的接头组装槽103中。详细来说，可挠性主体10a具有二开口102，分别位于可挠性主体10a的相异侧，且各该开口102形成于其中二可变形部102之间，接头组装槽103位于可挠性主体10a中且分别经由该二开口102连通于外，螺钉接头20位于接头组装槽103中，且仅部分经由开口102暴露于外，但其余部分受到开口102周围的可变形部102阻挡而隐藏于可挠性主体10a中。或者说，在本实施例或其他实施例中，螺钉接头20于垂直方向上的长度至少大于开口102于垂直方向上的长度，其中，这里或后续所述的垂直方向是指以附图的视角来看，但本发明并非以此空间性用语为限。
另外，需注意的是，椎骨重建植入物1a可以但不限于是以3D打印技术于同一成型步骤所制成，也就是说，可挠性主体10a以及螺钉接头20可同时成型并于成型时自组装完成而构成如图2所示的椎骨重建植入物1a，或者说，螺钉接头20于可挠性主体10a成型过程中即同时成型于可挠性主体10a的接头组装槽103中，故可挠性主体10a与螺钉接头20成型后无需再进行组装程序，且螺钉接头20即不能经由开口102从接头组装槽103中取出。于此，可理解的是，在本实施例与其他实施例中，螺钉接头20也是一体成型的单体结构。
螺钉接头20可供前述的椎根螺钉81锁固组装，以使椎根螺钉81可活动地设置于可挠性主体10a上。详细来说，在本实施例与其他实施例中，螺钉接头20至少包含一显露部210以及至少二嵌入部220，显露部210衔接于嵌入部220之间，嵌入部220是为螺钉接头20上嵌入可挠性主体10a的接头组装槽103中且隐藏于可挠性主体10a中的部位，而显露部210是为螺钉接头20上位于接头组装槽103中但可从开口102暴露于外的部位。
在本实施例中，螺钉接头20的嵌入部220实质上略呈锥形，相应地，接头组装槽103中未直接从开口102暴露于外的部分可为形状匹配嵌入部220的锥形。由此配置，螺钉接头20得以在可挠性主体10a中进行转动。但本发明并非以螺钉接头20以及与其匹配的接头组装槽103的外形为限，例如于一些其他实施例中，螺钉接头可改为一球体，相应地，接头组装槽用于容置螺钉接头的部分可改为球形槽，由此，螺钉接头得以在可挠性主体中进行更多方向的转动运动。或者，在另一些其他实施例中，螺钉接头也可于垂直方向突设有凸点或柱状结构，以对应枢设于接头组装槽中的孔洞，在此配置下，螺钉接头也可在接头组装槽中进行枢转运动，且在此情况下，可挠性主体的开口于垂直方向上的长度可以实质上等于螺钉接头于垂直方向上的长度。
在本实施例与其他实施例中，显露部210是为螺钉接头20上供椎根螺钉81锁固组装的部位，如图所示，显露部210具有一锁孔211，适于供椎根螺钉81锁入对接。由此，椎根螺钉81可通过固定于螺钉接头20的方式可活动地设置于可挠性主体10a。由此，医师则可轻易地将椎根螺钉81调整至所需的角度。在一些实施例中，椎骨重建植入物1a可让椎根螺钉81具有约0～150度的角度调整幅度。另外，补充说明的是，螺钉接头20在可挠性主体10a上的位置不特别予以限制，应可依据实际患者的需求进行调整。
进一步地，在本实施例与其他实施例中，螺钉接头20的显露部210的锁孔211为一穿孔，可供螺锁并贯穿显露部210，并且，可挠性主体10a还具有至少一螺钉抵接内壁面108，位于接头组装槽103中且可经由显露部210的锁孔211及可挠性主体10a的开口102暴露于外。因此，当医师将椎根螺钉81锁于螺钉接头20并通过螺钉接头20将椎根螺钉81调整至合适的位置时，医师可再进一步地将椎根螺钉81贯穿锁孔211而抵接于螺钉接头20后方的可挠性主体10a内的螺钉抵接内壁面108，椎根螺钉81与螺钉抵接内壁面108之间的相互抵紧除了可产生摩擦力以防固定椎根螺钉81，还可迫使螺钉接头20往开口102方向移动而抵紧接头组装槽103的内壁面，从而将椎根螺钉81固定于当下的角度，以防止椎根螺钉81相对可挠性主体10a随意活动。
接着，请参阅图5，图5为图1的椎骨重建植入物1a受力时的示意图，需声明的是，为便于说明以及达到附图简洁的目的，图5中省略绘示椎根螺钉81。椎骨重建植入物1a被植入椎骨91间后，除了具有足够刚性以提供椎骨91有效地支撑效果而维持椎骨91于合适的高度，但当患者进行日常活动而使椎骨91的相对位置改变时，椎骨重建植入物1a的可变形部102可受到椎骨91的施压而相应产生形变，除了可缓冲并分散施加于椎骨重建植入物1a上的压力以避免应力集中于椎骨重建植入物1a与椎骨91接合处，还可配合椎骨91的活动以避免因椎骨91的移动而导致从椎骨91间滑脱的问题。经实际模拟结果，本发明前述实施例的椎骨重建植入物1a至少可具有往前后左右四个不同方向偏摆约0～20度的可挠性，且垂直方向的最大可压缩量可至约3毫米。
于此需声明的是，前述仅是本发明中实现可挠性的其中一种实施态样，本发明并非以此为限。例如请参阅6，图6为依据本发明的另一实施例的椎骨重建植入物1b的侧视图。然为达简洁说明的目的，以下仅针对本实施例与前述实施例的主要差异处进行说明，其余相似或相同之处可参阅前述说明中得知。
如图6所示，在本实施例中，椎骨重建植入物1b的可挠性主体10b为一个螺旋状的单体结构，类似于压缩弹簧，因此同样具有多方向的可挠性以及可压缩性。因此，同样可达到如前述实施例中避免应力集中及滑脱等效果。但本发明并非以螺旋结构的可挠性主体10b中每层实体结构之间的间距或每层实体结构的厚度等规格设计为限制，这些均可依据实际需求进行设计上的调整。甚至，例如于另一些其他实施例中，可挠性主体也可以改成是仅具有多孔结构107的块体，可挠性主体中的多孔结构107的数量可增加至使其达到所预期的可压缩性及可挠性的程度。
或者，请参阅图7A～图7B，图7A为依据本发明的又一实施例的椎骨重建植入物1c的立体分解示意图，而图7B为图7A的椎骨重建植入物1c的使用示意图。需先声明的是，为达简洁说明的目的，以下仅针对本实施例与前述实施例的主要差异处进行说明，其余相似或相同之处可参阅前述说明中得知。
如图所示，在本实施例中，椎骨重建植入物1c可包含两个彼此相互独立的可挠性主体：一第一可挠性主体10c以及一第二可挠性主体11c，第一可挠性主体10c与第二可挠性主体11c的结构可以但不限于相似或相同于前述实施例的可挠性主体，故于此不再赘述。
椎骨重建植入物1c还包含一衔接件30c，第一可挠性主体10c与第二可挠性主体11c分别可枢转地结合于衔接件30c的相对两侧。具体来说，在本实施例中，衔接件30c可以但不限于包含一衔接杆部310c及一间隔部320c，衔接杆部310c呈一杆状，间隔部320呈一盘状，衔接杆部310c穿设间隔部320，第一可挠性主体10c与第二可挠性主体11c分别可枢转地结合于衔接杆部310c穿出于间隔部320相对两侧的部分。补充说明的是，衔接件30c可以但不限于是一体成型的单体结构。此外，第一可挠性主体10c与第二可挠性主体11c可以但不限于仅是直接套设于衔接杆部310c上。
由此配置，第一可挠性主体10c与第二可挠性主体11c除了如前述实施例同样可达到受压迫时产生形变以缓解应力集中的效果，第一可挠性主体10c与第二可挠性主体11c还可彼此相对进行转动运动，从而可配合椎骨彼此之间产生较大幅度的旋转运动，如图7B中所示可相对第一可挠性主体10c往箭头方向转动的第二可挠性主体11c。于此，补充说明的是，在使用上，第一可挠性主体10c与第二可挠性主体11c可能会经常性与衔接件30c产生摩擦，因此为延长椎骨重建植入物1c的耐用度，衔接件30c可以但不限于以耐磨高分子或陶瓷等材料所制成。
又或者，请参阅图8A为依据本发明的再一实施例的椎骨重建植入物1d的立体示意图，而图8B为图8A的椎骨重建植入物1d的使用示意图。需先声明的是，为达简洁说明的目的，以下仅针对本实施例与前述实施例的主要差异处进行说明，其余相似或相同之处可参阅前述说明中得知。
如图所示，在本实施例中，椎骨重建植入物1d的衔接件30d的衔接杆部310d为一螺杆，其相对两端分别螺锁进入椎骨重建植入物1d的第一可挠性主体10d以及第二可挠性主体11d，而衔接件30d的间隔部320d则为固定于第一可挠性主体10d上且可供衔接杆部310d螺锁穿设的结构。
由此配置，第一可挠性主体10d与第二可挠性主体11d除了如前述实施例同样可达到受压迫时产生形变以缓解应力集中的效果，第一可挠性主体10d与第二可挠性主体11d还可通过衔接件30d调整其之间的间距，以进一步配合椎骨需要被调整的高度。如图8B中所示，第二可挠性主体11d可沿衔接件30d的衔接杆部310d往箭头方向相对靠近或远离第一可挠性主体10d。在一些实施例中，第二可挠性主体11d相对第一可挠性主体10d可被调整的最远距离可使椎骨重建植入物1d具有约20～100毫米的高度变化，或是使椎骨重建植入物约具有其原始高度的10～80％的高度增加量。
由本发明前述实施例的椎骨重建植入物，通过一体成型的可挠性主体，使得椎骨重建植入物具有足以维持椎骨相对位置的刚性的同时，还具有可配合人体活动的可挠性与可压缩性，以减低或缓冲人体活动时来自椎骨的压力，不仅可避免从椎骨间滑脱的问题，还可避免与邻接的椎骨之间产生应力集中而破坏椎骨的问题。由此，可避免椎骨重建手术后如椎骨受损病变或退化、植入物滑脱或融合失败等问题的发生。
并且，通过一体成型且可活动地位于可挠性主体中的螺钉接头，便于医师于手术过程中调整椎根螺钉的角度，从而助于手术的进行。

Claims (10)

1.一种椎骨重建植入物，其特征在于，包含：
可挠性主体，为一体成型的单体结构，且具有彼此相连通的至少一接头组装槽以及至少一开口；以及
至少一螺钉接头，为一体成型的单体结构，该至少一螺钉接头可活动地容置于该至少一接头组装槽中。
2.如权利要求1所述的椎骨重建植入物，其中该至少一螺钉接头包含一显露部以及二嵌入部，该显露部衔接于该二嵌入部之间，该显露部具有锁孔，且该至少一螺钉接头中仅该显露部经由该至少一开口暴露于外。
3.如权利要求2所述的椎骨重建植入物，其中该可挠性主体具有至少一螺钉抵接内壁面，该至少一螺钉抵接内壁面位于该至少一接头组装槽中且经由该显露部的该锁孔以及该至少一开口暴露于外。
4.如权利要求1所述的椎骨重建植入物，其中该可挠性主体与该至少一螺钉接头为于同一3D成型步骤所制成。
5.如权利要求1所述的椎骨重建植入物，其中该可挠性主体有多个沟槽，该些沟槽彼此相对间隔地交错配置。
6.如权利要求1所述的椎骨重建植入物，其中该可挠性主体为一体成型的螺旋状单体结构。
7.如权利要求1所述的椎骨重建植入物，其中该可挠性主体具有二椎骨接触面以及多个牙状结构，该些牙状结构突设于该些椎骨接触面，且沿着该椎骨接触面的外轮廓排列。
8.如权利要求1所述的椎骨重建植入物，还包含衔接件以及另一可挠性主体，该可挠性主体与该另一可挠性主体经由该衔接件可枢转地彼此相连接。
9.如权利要求8所述的椎骨重建植入物，其中该衔接件包含衔接杆部以及间隔部，该可挠性主体可枢转地设置于该衔接杆部的一端，该另一可挠性主体可枢转地设置于该衔接杆部的另一端，该衔接杆部穿设该间隔部，该间隔部夹设于该可挠性主体与该另一可挠性主体之间。
10.如权利要求8所述的椎骨重建植入物，其中该衔接件包含衔接杆部以及间隔部，该衔接杆部为螺杆，该衔接杆部的一端螺锁于该可挠性主体，该衔接杆部的一端螺锁于该另一可挠性主体，该衔接杆部穿设该间隔部，该间隔部介于该可挠性主体与该另一可挠性主体之间。
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